Low-field diffusion weighted imaging

ABSTRACT

Methods and apparatus for operating a low-field magnetic resonance imaging (MRI) system to perform diffusion weighted imaging, the low-field MRI system including a plurality of magnetics components including a B 0  magnet configured to produce a low-field main magnetic field B 0 , at least one gradient coil configured to, when operated, provide spatial encoding of emitted magnetic resonance signals, and at least one radio frequency (RF) component configured to acquire, when operated, the emitted magnetic resonance signals. The method comprises controlling one or more of the plurality of magnetics components in accordance with at least one pulse sequence having a diffusion-weighted gradient encoding period followed by multiple echo periods during which magnetic resonance signals are produced and detected, wherein at least two of the multiple echo periods correspond to respective encoded echoes having an opposite gradient polarity.

RELATED APPLICATIONS

This application claims the benefit under 35 U.S.C. § 120 and is acontinuation application of U.S. patent application Ser. No. 16/527,327,filed Jul. 31, 2019, entitled “LOW-FIELD DIFFUSION WEIGHTED IMAGING”,which claims priority under 35 U.S.C. § 119(e) to U.S. ProvisionalApplication No. 62/712,565, filed Jul. 31, 2018 and titled, “LOW-FIELDDIFFUSION WEIGHTED IMAGING,” each application of which is incorporatedby reference herein in its entirety.

BACKGROUND

Magnetic resonance imaging (MRI) provides an important imaging modalityfor numerous applications and is widely utilized in clinical andresearch settings to produce images of the inside of the human body. Asa generality, MRI is based on detecting magnetic resonance (MR) signals,which are electromagnetic waves emitted by atoms in response to statechanges resulting from applied electromagnetic fields. For example,nuclear magnetic resonance (NMR) techniques involve detecting MR signalsemitted from the nuclei of excited atoms upon the re-alignment orrelaxation of the nuclear spin of atoms in an object being imaged (e.g.,atoms in the tissue of the human body). Detected MR signals may beprocessed to produce images, which in the context of medicalapplications, allows for the investigation of internal structures and/orbiological processes within the body for diagnostic, therapeutic and/orresearch purposes.

MRI provides an attractive imaging modality for biological imaging dueto the ability to produce non-invasive images having relatively highresolution and contrast without the safety concerns of other modalities(e.g., without needing to expose the subject to ionizing radiation,e.g., x-rays, or introducing radioactive material to the body).Additionally, MRI is particularly well suited to provide soft tissuecontrast, which can be exploited to image subject matter that otherimaging modalities are incapable of satisfactorily imaging. Moreover, MRtechniques are capable of capturing information about structures and/orbiological processes that other modalities are incapable of acquiring.However, there are a number of drawbacks to MRI that, for a givenimaging application, may involve the relatively high cost of theequipment, limited availability and/or difficulty in gaining access toclinical MRI scanners and/or the length of the image acquisitionprocess.

The trend in clinical MRI has been to increase the field strength of MRIscanners to improve one or more of scan time, image resolution, andimage contrast, which, in turn, continues to drive up costs. The vastmajority of installed MRI scanners operate at 1.5 or 3 tesla (T), whichrefers to the field strength of the main magnetic field B₀. A rough costestimate for a clinical MRI scanner is approximately one million dollarsper tesla, which does not factor in the substantial operation, service,and maintenance costs involved in operating such MRI scanners.

Additionally, conventional high-field MRI systems typically requirelarge superconducting magnets and associated electronics to generate astrong uniform static magnetic field (B₀) in which an object (e.g., apatient) is imaged. The size of such systems is considerable with atypical MRI installment including multiple rooms for the magnet,electronics, thermal management system, and control console areas. Thesize and expense of MRI systems generally limits their usage tofacilities, such as hospitals and academic research centers, which havesufficient space and resources to purchase and maintain them. The highcost and substantial space requirements of high-field MRI systemsresults in limited availability of MRI scanners. As such, there arefrequently clinical situations in which an MRI scan would be beneficial,but due to one or more of the limitations discussed above, is notpractical or is impossible, as discussed in further detail below.

SUMMARY

Some embodiments are directed to a low-field magnetic resonance imaging(MRI) system. The low-field MRI system comprises a plurality ofmagnetics components including a B₀ magnet configured to produce alow-field main magnetic field B₀, at least one gradient coil configuredto, when operated, provide spatial encoding of emitted magneticresonance signals, at least one radio frequency (RF) componentconfigured to acquire, when operated, the emitted magnetic resonancesignals, and at least one controller. The at least one controller isconfigured to operate one or more of the plurality of magneticscomponents in accordance with at least one pulse sequence having adiffusion-weighted gradient encoding period followed by multiple echoperiods during which magnetic resonance signals are produced anddetected, wherein at least two of the multiple echo periods correspondto respective encoded echoes having an opposite gradient polarity.

Some embodiments are directed to a computer-implemented method ofoperating a low-field magnetic resonance imaging (MRI) system to performdiffusion weighted imaging, the low-field MRI system including aplurality of magnetics components including a B₀ magnet configured toproduce a low-field main magnetic field B₀, at least one gradient coilconfigured to, when operated, provide spatial encoding of emittedmagnetic resonance signals, and at least one radio frequency (RF)component configured to acquire, when operated, the emitted magneticresonance signals. The method comprising controlling one or more of theplurality of magnetics components in accordance with at least one pulsesequence having a diffusion-weighted gradient encoding period followedby multiple echo periods during which magnetic resonance signals areproduced and detected, wherein at least two of the multiple echo periodscorrespond to respective encoded echoes having an opposite gradientpolarity.

Some embodiments are directed to a non-transitory computer-readablemedium encoded with a plurality of instructions that, when executed byat least one computer processor, cause the at least one computerprocessor to perform a method of operating a low-field magneticresonance imaging (MRI) system to perform diffusion weighted imaging,the low-field MRI system including a plurality of magnetics componentsincluding a B₀ magnet configured to produce a low-field main magneticfield B₀, at least one gradient coil configured to, when operated,provide spatial encoding of emitted magnetic resonance signals, and atleast one radio frequency (RF) component configured to acquire, whenoperated, the emitted magnetic resonance signals. The method comprisescontrolling one or more of the plurality of magnetics components inaccordance with at least one pulse sequence having a diffusion-weightedgradient encoding period followed by multiple echo periods during whichmagnetic resonance signals are produced and detected, wherein at leasttwo of the multiple echo periods correspond to respective encoded echoeshaving an opposite gradient polarity.

It should be appreciated that all combinations of the foregoing conceptsand additional concepts discussed in greater detail below (provided suchconcepts are not mutually inconsistent) are contemplated as being partof the inventive subject matter disclosed herein. In particular, allcombinations of claimed subject matter appearing at the end of thisdisclosure are contemplated as being part of the inventive subjectmatter disclosed herein.

BRIEF DESCRIPTION OF DRAWINGS

Various non-limiting embodiments of the technology will be describedwith reference to the following figures. It should be appreciated thatthe figures are not necessarily drawn to scale.

FIG. 1 illustrates exemplary components of a low-field magneticresonance imaging system that may be controlled to performdiffusion-weighted imaging in accordance with some embodiments;

FIG. 2 illustrates a pulse sequence that may be used to performdiffusion-weighted imaging using a low-field magnetic resonance imagingsystem in accordance with some embodiments.

FIG. 3 illustrates a process for correcting image blurring caused duringdiffusion-weighted imaging using a low-field magnetic resonance imagingsystem in accordance with some embodiments;

FIG. 4 illustrates a process for improving image quality by usingmultiple echo periods in a diffusion-weighted imaging pulse sequence inaccordance with some embodiments; and

FIGS. 5A-5C illustrate images generated using the process shown in FIG.4.

DETAILED DESCRIPTION

The MRI scanner market is overwhelmingly dominated by high-fieldsystems, and particularly for medical or clinical MRI applications. Asdiscussed above, the general trend in medical imaging has been toproduce MRI scanners with increasingly greater field strengths, with thevast majority of clinical MRI scanners operating at 1.5 T or 3 T, withhigher field strengths of 7 T and 9 T used in research settings. As usedherein, “high-field” refers generally to MRI systems presently in use ina clinical setting and, more particularly, to MRI systems operating witha main magnetic field (i.e., a B₀ field) at or above 1.5 T, thoughclinical systems operating between 0.5 T and 1.5 T are often alsocharacterized as “high-field.” Field strengths between approximately 0.2T and 0.5 T have been characterized as “mid-field” and, as fieldstrengths in the high-field regime have continued to increase, fieldstrengths in the range between 0.5 T and 1 T have also beencharacterized as mid-field. By contrast, “low-field” refers generally toMRI systems operating with a B₀ field of less than or equal toapproximately 0.2 T, though systems having a B₀ field of between 0.2 Tand approximately 0.3 T have sometimes been characterized as low-fieldas a consequence of increased field strengths at the high end of thehigh-field regime. Within the low-field regime, low-field MRI systemsoperating with a B₀ field of less than 0.1 T are referred to herein as“very low-field” and low-field MRI systems operating with a B₀ field ofless than 10 mT are referred to herein as “ultra-low field.”

As discussed above, conventional MRI systems require specializedfacilities. An electromagnetically shielded room is required for the MRIsystem to operate and the floor of the room must be structurallyreinforced. Additional rooms must be provided for the high-powerelectronics and the scan technician's control area. Secure access to thesite must also be provided. In addition, a dedicated three-phaseelectrical connection must be installed to provide the power for theelectronics that, in turn, are cooled by a chilled water supply.Additional HVAC capacity typically must also be provided. These siterequirements are not only costly, but significantly limit the locationswhere MRI systems can be deployed. Conventional clinical MRI scannersalso require substantial expertise to both operate and maintain. Thesehighly trained technicians and service engineers add large on-goingoperational costs to operating an MRI system. Conventional MRI, as aresult, is frequently cost prohibitive and is severely limited inaccessibility, preventing MRI from being a widely available diagnostictool capable of delivering a wide range of clinical imaging solutionswherever and whenever needed. Typically, a patient must visit one of alimited number of facilities at a time and place scheduled in advance,preventing MRI from being used in numerous medical applications forwhich it is uniquely efficacious in assisting with diagnosis, surgery,patient monitoring and the like.

As discussed above, high-field MRI systems require specially adaptedfacilities to accommodate the size, weight, power consumption andshielding requirements of these systems. For example, a 1.5 T MRI systemtypically weighs between 4-10 tons and a 3 T MRI system typically weighsbetween 8-20 tons. In addition, high-field MRI systems generally requiresignificant amounts of heavy and expensive shielding. Many mid-fieldscanners are even heavier, weighing between 10-20 tons due, in part, tothe use of very large permanent magnets and/or yokes. Commerciallyavailable low-field MRI systems (e.g., operating with a B₀ magneticfield of 0.2 T) are also typically in the range of 10 tons or more duethe large of amounts of ferromagnetic material used to generate the B₀field, with additional tonnage in shielding. To accommodate this heavyequipment, rooms (which typically have a minimum size of 30-50 squaremeters) have to be built with reinforced flooring (e.g., concreteflooring), and must be specially shielded to prevent electromagneticradiation from interfering with operation of the MRI system. Thus,available clinical MRI systems are immobile and require the significantexpense of a large, dedicated space within a hospital or facility, andin addition to the considerable costs of preparing the space foroperation, require further additional on-going costs in expertise inoperating and maintaining the system.

In addition, currently available MRI systems typically consume largeamounts of power. For example, common 1.5 T and 3 T MRI systemstypically consume between 20-40 kW of power during operation, whileavailable 0.5 T and 0.2 T MRI systems commonly consume between 5-20 kW,each using dedicated and specialized power sources. Unless otherwisespecified, power consumption is referenced as average power consumedover an interval of interest. For example, the 20-40 kW referred toabove indicates the average power consumed by conventional MRI systemsduring the course of image acquisition, which may include relativelyshort periods of peak power consumption that significantly exceeds theaverage power consumption (e.g., when the gradient coils and/or RF coilsare pulsed over relatively short periods of the pulse sequence).Intervals of peak (or large) power consumption are typically addressedvia power storage elements (e.g., capacitors) of the MRI system itself.Thus, the average power consumption is the more relevant number as itgenerally determines the type of power connection needed to operate thedevice. As discussed above, available clinical MRI systems must havededicated power sources, typically requiring a dedicated three-phaseconnection to the grid to power the components of the MRI system.Additional electronics are then needed to convert the three-phase powerinto single-phase power utilized by the MRI system. The many physicalrequirements of deploying conventional clinical MRI systems creates asignificant problem of availability and severely restricts the clinicalapplications for which MRI can be utilized.

Accordingly, the many requirements of high-field MRI renderinstallations prohibitive in many situations, limiting their deploymentto large institutional hospitals or specialized facilities and generallyrestricting their use to tightly scheduled appointments, requiring thepatient to visit dedicated facilities at times scheduled in advance.Thus, the many restrictions on high-field MRI prevent MRI from beingfully utilized as an imaging modality. Despite the drawbacks ofhigh-field MRI mentioned above, the appeal of the significant increasein signal-to-noise ratio (SNR) at higher fields continues to drive theindustry to higher and higher field strengths for use in clinical andmedical MRI applications, further increasing the cost and complexity ofMRI scanners, and further limiting their availability and preventingtheir use as a general-purpose and/or generally-available imagingsolution.

The low SNR of MR signals produced in the low-field regime (particularlyin the very low-field regime) has prevented the development of arelatively low cost, low power and/or portable MRI system. Conventional“low-field” MRI systems operate at the high end of what is typicallycharacterized as the low-field range (e.g., clinically availablelow-field systems have a floor of approximately 0.2 T) to achieve usefulimages. Though somewhat less expensive then high-field MRI systems,conventional low-field MRI systems share many of the same drawbacks. Inparticular, conventional low-field MRI systems are large, fixed andimmobile installments, consume substantial power (requiring dedicatedthree-phase power hook-ups) and require specially shielded rooms andlarge dedicated spaces. The challenges of low-field MRI have preventedthe development of relatively low cost, low power and/or portable MRIsystems that can produce useful images.

The inventors have developed techniques enabling portable, low-field,low power and/or lower-cost MRI systems that can improve the wide-scaledeployability of MRI technology in a variety of environments beyond thecurrent MRI installments at hospitals and research facilities. As aresult, MRI can be deployed in emergency rooms, small clinics, doctor'soffices, in mobile units, in the field, etc. and may be brought to thepatient (e.g., bedside) to perform a wide variety of imaging proceduresand protocols. Some embodiments include very low-field MRI systems(e.g., 0.1 T, 50 mT, 20 mT, etc.) that facilitate portable, low-cost,low-power MRI, significantly increasing the availability of MRI in aclinical setting.

There are numerous challenges to developing a clinical MRI system in thelow-field regime. As used herein, the term clinical MRI system refers toan MRI system that produces clinically useful images, which refers toimages having sufficient resolution and adequate acquisition times to beuseful to a physician or clinician for its intended purpose given aparticular imaging application. As such, the resolutions/acquisitiontimes of clinically useful images will depend on the purpose for whichthe images are being obtained. Among the numerous challenges inobtaining clinically useful images in the low-field regime is therelatively low SNR. Specifically, the relationship between SNR and B₀field strength is approximately B₀ ^(5/4) at field strength above 0.2 Tand approximately B₀ ^(3/2) at field strengths below 0.1 T. As such, theSNR drops substantially with decreases in field strength with even moresignificant drops in SNR experienced at very low field strength. Thissubstantial drop in SNR resulting from reducing the field strength is asignificant factor that has prevented development of clinical MRIsystems in the very low-field regime. In particular, the challenge ofthe low SNR at very low field strengths has prevented the development ofa clinical MRI system operating in the very low-field regime. As aresult, clinical MRI systems that seek to operate at lower fieldstrengths have conventionally achieved field strengths of approximatelythe 0.2 T range and above. These MRI systems are still large, heavy andcostly, generally requiring fixed dedicated spaces (or shielded tents)and dedicated power sources.

The inventors have developed low-field and very low-field MRI systemscapable of producing clinically useful images, allowing for thedevelopment of portable, low cost and easy to use MRI systems notachievable using state of the art technology. According to someembodiments, an MRI system can be transported to the patient to providea wide variety of diagnostic, surgical, monitoring and/or therapeuticprocedures, generally, whenever and wherever needed.

FIG. 1 is a block diagram of typical components of a MRI system 100. Inthe illustrative example of FIG. 1, MRI system 100 comprises computingdevice 104, controller 106, pulse sequences store 108, power managementsystem 110, and magnetics components 120. It should be appreciated thatsystem 100 is illustrative and that a MRI system may have one or moreother components of any suitable type in addition to or instead of thecomponents illustrated in FIG. 1. However, a MRI system will generallyinclude these high level components, though the implementation of thesecomponents for a particular MRI system may differ vastly, as discussedin further detail below.

As illustrated in FIG. 1, magnetics components 120 comprise B₀ magnet122, shim coils 124, RF transmit and receive coils 126, and gradientcoils 128. Magnet 122 may be used to generate the main magnetic fieldB₀. Magnet 122 may be any suitable type or combination of magneticscomponents that can generate a desired main magnetic B₀ field. Asdiscussed above, in the high field regime, the B₀ magnet is typicallyformed using superconducting material generally provided in a solenoidgeometry, requiring cryogenic cooling systems to keep the B₀ magnet in asuperconducting state. Thus, high-field B₀ magnets are expensive,complicated and consume large amounts of power (e.g., cryogenic coolingsystems require significant power to maintain the extremely lowtemperatures needed to keep the B₀ magnet in a superconducting state),require large dedicated spaces, and specialized, dedicated powerconnections (e.g., a dedicated three-phase power connection to the powergrid). Conventional low-field B₀ magnets (e.g., B₀ magnets operating at0.2 T) are also often implemented using superconducting material andtherefore have these same general requirements. Other conventionallow-field B₀ magnets are implemented using permanent magnets, which toproduce the field strengths to which conventional low-field systems arelimited (e.g., between 0.2 T and 0.3 T due to the inability to acquireuseful images at lower field strengths), need to be very large magnetsweighing 5-20 tons. Thus, the B₀ magnet of conventional MRI systemsalone prevents both portability and affordability.

Gradient coils 128 may be arranged to provide gradient fields and, forexample, may be arranged to generate gradients in the B₀ field in threesubstantially orthogonal directions (X, Y, Z). Gradient coils 128 may beconfigured to encode emitted MR signals by systematically varying the B₀field (the B₀ field generated by magnet 122 and/or shim coils 124) toencode the spatial location of received MR signals as a function offrequency or phase. For example, gradient coils 128 may be configured tovary frequency or phase as a linear function of spatial location along aparticular direction, although more complex spatial encoding profilesmay also be provided by using nonlinear gradient coils. For example, afirst gradient coil may be configured to selectively vary the B₀ fieldin a first (X) direction to perform frequency encoding in thatdirection, a second gradient coil may be configured to selectively varythe B₀ field in a second (Y) direction substantially orthogonal to thefirst direction to perform phase encoding, and a third gradient coil maybe configured to selectively vary the B₀ field in a third (Z) directionsubstantially orthogonal to the first and second directions to enableslice selection for volumetric imaging applications. As discussed above,conventional gradient coils also consume significant power, typicallyoperated by large, expensive gradient power sources, as discussed infurther detail below.

MRI is performed by exciting and detecting emitted MR signals usingtransmit and receive coils, respectively (often referred to as radiofrequency (RF) coils). Transmit/receive coils may include separate coilsfor transmitting and receiving, multiple coils for transmitting and/orreceiving, or the same coils for transmitting and receiving. Thus, atransmit/receive component may include one or more coils fortransmitting, one or more coils for receiving and/or one or more coilsfor transmitting and receiving. Transmit/receive coils are also oftenreferred to as Tx/Rx or Tx/Rx coils to generically refer to the variousconfigurations for the transmit and receive magnetics component of anMRI system. These terms are used interchangeably herein. In FIG. 1, RFtransmit and receive coils 126 comprise one or more transmit coils thatmay be used to generate RF pulses to induce an oscillating magneticfield Bi. The transmit coil(s) may be configured to generate anysuitable types of RF pulses.

Power management system 110 includes electronics to provide operatingpower to one or more components of the low-field MRI system 100. Forexample, as discussed in more detail below, power management system 110may include one or more power supplies, gradient power components,transmit coil components, and/or any other suitable power electronicsneeded to provide suitable operating power to energize and operatecomponents of MRI system 100. As illustrated in FIG. 1, power managementsystem 110 comprises power supply 112, power component(s) 114,transmit/receive switch 116, and thermal management components 118(e.g., cryogenic cooling equipment for superconducting magnets). Powersupply 112 includes electronics to provide operating power to magneticcomponents 120 of the MRI system 100. For example, power supply 112 mayinclude electronics to provide operating power to one or more B₀ coils(e.g., B₀ magnet 122) to produce the main magnetic field for thelow-field MRI system. Transmit/receive switch 116 may be used to selectwhether RF transmit coils or RF receive coils are being operated.

Power component(s) 114 may include one or more RF receive (Rx)pre-amplifiers that amplify MR signals detected by one or more RFreceive coils (e.g., coils 126), one or more RF transmit (Tx) powercomponents configured to provide power to one or more RF transmit coils(e.g., coils 126), one or more gradient power components configured toprovide power to one or more gradient coils (e.g., gradient coils 128),and one or more shim power components configured to provide power to oneor more shim coils (e.g., shim coils 124).

In conventional MRI systems, the power components are large, expensiveand consume significant power. Typically, the power electronics occupy aroom separate from the MRI scanner itself. The power electronics notonly require substantial space, but are expensive complex devices thatconsume substantial power and require wall mounted racks to besupported. Thus, the power electronics of conventional MRI systems alsoprevent portability and affordable of MRI.

As illustrated in FIG. 1, MRI system 100 includes controller 106 (alsoreferred to as a console) having control electronics to sendinstructions to and receive information from power management system110. Controller 106 may be configured to implement one or more pulsesequences, which are used to determine the instructions sent to powermanagement system 110 to operate the magnetic components 120 in adesired sequence (e.g., parameters for operating the RF transmit andreceive coils 126, parameters for operating gradient coils 128, etc.).As illustrated in FIG. 1, controller 106 also interacts with computingdevice 104 programmed to process received MR data. For example,computing device 104 may process received MR data to generate one ormore MR images using any suitable image reconstruction process(es).Controller 106 may provide information about one or more pulse sequencesto computing device 104 for the processing of data by the computingdevice. For example, controller 106 may provide information about one ormore pulse sequences to computing device 104 and the computing devicemay perform an image reconstruction process based, at least in part, onthe provided information. In conventional MRI systems, computing device104 typically includes one or more high performance work-stationsconfigured to perform computationally expensive processing on MR datarelatively rapidly. Such computing devices are relatively expensiveequipment on their own.

As should be appreciated from the foregoing, currently availableclinical MRI systems (including high-field, mid-field and low-fieldsystems) are large, expensive, fixed installations requiring substantialdedicated and specially designed spaces, as well as dedicated powerconnections. The inventors have developed low-field, including very-lowfield, MRI systems that are lower cost, lower power and/or portable,significantly increasing the availability and applicability of MRI.According to some embodiments, a portable MRI system is provided,allowing an MRI system to be brought to the patient and utilized atlocations where it is needed.

As discussed above, some embodiments include an MRI system that isportable, allowing the MRI device to be moved to locations in which itis needed (e.g., emergency and operating rooms, primary care offices,neonatal intensive care units, specialty departments, emergency andmobile transport vehicles and in the field). There are numerouschallenges that face the development of a portable MRI system, includingsize, weight, power consumption and the ability to operate in relativelyuncontrolled electromagnetic noise environments (e.g., outside aspecially shielded room).

An aspect of portability involves the capability of operating the MRIsystem in a wide variety of locations and environments. As discussedabove, currently available clinical MRI scanners are required to belocated in specially shielded rooms to allow for correct operation ofthe device and is one (among many) of the reasons contributing to thecost, lack of availability and non-portability of currently availableclinical MRI scanners. Thus, to operate outside of a specially shieldedroom and, more particularly, to allow for generally portable, cartableor otherwise transportable MRI, the MRI system must be capable ofoperation in a variety of noise environments. The inventors havedeveloped noise suppression techniques that allow the MRI system to beoperated outside of specially shielded rooms, facilitating bothportable/transportable MRI as well as fixed MRI installments that do notrequire specially shielded rooms. While the noise suppression techniquesallow for operation outside specially shielded rooms, these techniquescan also be used to perform noise suppression in shielded environments,for example, less expensive, loosely or ad-hoc shielding environments,and can be therefore used in conjunction with an area that has beenfitted with limited shielding, as the aspects are not limited in thisrespect.

A further aspect of portability involves the power consumption of theMRI system. As also discussed above, current clinical MRI systemsconsume large amounts of power (e.g., ranging from 20 kW to 40 kWaverage power consumption during operation), thus requiring dedicatedpower connections (e.g., dedicated three-phase power connections to thegrid capable of delivering the required power). The requirement of adedicated power connection is a further obstacle to operating an MRIsystem in a variety of locations other than expensive dedicated roomsspecially fitted with the appropriate power connections. The inventorshave developed low power MRI systems capable of operating using mainselectricity such as a standard wall outlet (e.g., 120V/20 A connectionin the U.S.) or common large appliance outlets (e.g., 220-240V/30 A),allowing the device to be operated anywhere common power outlets areprovided. The ability to “plug into the wall” facilitates bothportable/transportable MRI as well as fixed MRI system installationswithout requiring special, dedicated power such as a three-phase powerconnection.

Low-field MR has been explored in limited contexts for non-imagingresearch purposes and narrow and specific contrast-enhanced imagingapplications, but is conventionally regarded as being unsuitable forproducing clinically useful images. For example, the resolution,contrast, and/or image acquisition time is generally not regarded asbeing suitable for clinical purposes including, but not limited to,tissue differentiation, blood flow or perfusion imaging,diffusion-weighted (DW) or diffusion tensor (DT) imaging, functional MRI(fMRI), etc. At least some of the difficulty in obtaining clinicallyuseful images using low-field MRI relates to the fact that, generallyspeaking, pulse sequences designed for high-field MRI are unsuitable ina low-field environment.

The inventors have developed a technique for performingdiffusion-weighted imaging in the low-field environment. Currently,diffusion-weighted imaging (DWI) is the only MRI contrast that candirectly assess tissue microstructure, which is important for diagnosingstroke and other pathology. Performing DWI is technically challenging inthat DWI is an inherently low-SNR sequence and places high demands onMRI hardware including the gradient coils and amplifiers. Low-cost,low-field MR scanners amplify the technical challenges of implementingDWI. One example of a low-cost, low-field MR scanner is described inU.S. Pat. App. Pub. No. 2018/0164390, titled “Electromagnetic Shieldingfor Magnetic Resonance Imaging Methods and Apparatus,” which isincorporated by reference herein in its entirety.

To at least partially address some of the challenges of performing DWIat low field, the inventors have developed a pulse sequence referred toherein as the diffusion-weighted steady state free precession (DW-SSFP)sequence, that is specifically designed for use and/or optimalperformance in the low-field context. For example, the DW-SSFP sequencehas higher SNR efficiency and lower demands on gradient amplifiers thanconventional DWI sequences. The inventors have developed severalinnovations to enable a low-field MR scanner to perform the DW-SSFPsequence including, but not limited to, the ones described below.

FIG. 2 schematically illustrates a time-sequence of aspects of theDW-SSFP sequence in accordance with some embodiments. In particular,FIG. 2 illustrates a radio-frequency (RF) time sequence indicating timeswhen the RF coil is transmitting an RF pulse (e.g., RF pulse 210), adata acquisition (DAQ) time sequence indicating times when emittedmagnetic resonance signals are being acquired by the MR receive coils,and a gradient time sequence indicating times when the x-, y-, andz-gradients are activated to provide spatial encoding of the emitted MRsignals.

Conventional DWI sequences place large demands on gradient amplifiersand coils. The gradient coils warm up with use and the heat generated bythe gradient coils is transferred to their surroundings, including themagnet blocks that generate the main B₀ field in the low-field MRscanner. Consequently, the B₀ field produced by the magnet blocks lowersas a result of heating from excessive gradient coil use in conventionalDWI sequences. Changes in the generated B₀ field due to heating causethe reconstructed image to shift along the readout direction, resultingin blurring along that direction. To at least partially mitigate theheating-induced field drift of the B₀ magnet, the DW-SSFP sequenceincludes an RF pulse 210 immediately followed by a readout period 220during which magnetic resonance data is acquired, as shown in FIG. 2.

FIG. 3 illustrates a process 300 for using magnetic resonance dataacquired during the readout period 220 immediately following the RFpulse 210 to correct image blurring due to B₀ field drift. In act 310,the phase of the free induction decay (FID) resulting from the RF pulseis captured during readout period 220. The slope of the phase of the FIDis directly proportional to the B₀ field strength. Process 300 thenproceeds to act 320, where the phase of the FID determined in act 310 isfit to a linear model to improve robustness to noise due to B₀ fielddrift. Process 300 then proceeds to act 330, where the fit phase is usedto remove the phase introduced into the acquired MR signals caused by B₀field drift, thereby correcting the blurring in the resulting images.

Some low-field MR scanners, such as the low-field scanner described inU.S. Pat. App. Pub. No. 2018/0164390, include gradient components thatproduce lower gradient amplitudes than a conventional high-field MRIsystem. However, as discussed above, diffusion weighted imaging requiresa substantial amount of gradient encoding. To reduce encoding time, itis desirable to use the maximum amplitude gradient possible. However,eddy current pre-emphasis, which is used for image correction, requiresextra room above the maximum gradient amplitude of any gradient encodingwaveform to perform pre-emphasis. Accordingly, trapezoidal waveforms forDW gradient encoding are generally prevented from using the maximumgradient due to the need to leave room for the eddy current pre-emphasisabove the maximum. To balance the desire to use maximum amplitudegradients and the need to include eddy current pre-emphasis, someembodiments of the DW-SSFP pulse sequence include a diffusion weightedencoding gradient waveform that is not trapezoidal. An example, of sucha waveform is shown in FIG. 2 and includes a shaped attack edge 230. Asshown, the shaped attack edge does not have a constant slope, but ratherhas a slope that decreases as the maximum value is approached. Theshaped attack edge ensures that the pre-emphasized resulting waveformhas a flat top at the maximum. As shown, the decay edge ofdiffusion-weighted encoding gradient waveform is unaffected, such thatpre-emphasis can be used to reduce the resulting eddy currents duringthe imaging block (corresponding to the time periods 240 and 250 in FIG.2).

As discussed above, low-field MRI systems by their design have lower SNRcompared to high-field MRI systems. As shown in FIG. 2, the diffusionweighted encoding gradients occur over a relatively long timespan and assuch, the available signal to be detected is reduced. To increase SNRefficiency, it is desired that the readout time followingdiffusion-weighted gradient encoding (also referred to herein as the“imaging block”) be as long as possible. However, the inhomogeneity ofthe B₀ field in some low-field scanners may cause longer readouts tohave blurring and image warping. As shown in FIG. 2, in someembodiments, the DW-SSFP sequence extends the imaging block by encodingmultiple echoes during time periods 240 and 250 in the imaging block.Although two echoes are shown in FIG. 2, it should be appreciated thatany number of echoes may alternatively be used in the DW-SSFP sequencein accordance with some embodiments. In a readout scheme with multipleencoded echoes, as shown, a line of k-space is measured during a firsttime period 240, the gradient polarity is reversed, and the same line ofk-space is measured again during a second time period 250. Such areadout scheme reduces encoding time and increases SNR efficiency.

The gradients used in DWI sequences are typically large, resulting inresidual eddy currents in the magnetic components of the low-field MRIsystem. The residual eddy currents cause warping of the image along theslowest encoding direction. Warping also arises from the inhomogeneousB₀ field, as noted above. In the multi-echo approach, an example ofwhich is shown in FIG. 2, the warping is in opposite directions foradjacent echoes in the pulse sequence (e.g., the echo encoded duringtime period 240 and the echo encoded during time period 250 haveopposite gradient polarities). By comparing the adjacent echoes havingopposite gradient polarities, the images can de-warped during imagereconstruction and the images can be combined to increase SNR.

FIG. 4 illustrates a process 400 for increasing SNR for diffusionweighted imaging using a pulse sequence with multiple echoes havingdifferent polarities in accordance with some embodiments. In act 410, MRsignals corresponding to a first gradient echo of the DW-SSFP pulsesequence (e.g., the echo encoded during time period 240) are acquired.FIG. 5A shows images reconstructed based on the MR signals acquiredduring time period 240. Process 400 then proceeds to act 420, where MRsignals corresponding to a second gradient echo of the DW-SSFP pulsesequence (e.g., the echo encoded during time period 250) are acquired.FIG. 5B shows images reconstructed based on the MR signals acquiredduring the time period 250. Process 400 then proceeds to act 430 wherethe images acquired during time period 240 and the images acquiredduring time period 250 are de-warped during image reconstruction.Process 400 then proceeds to act 440 where the de-warped images arecombined. FIG. 4C shows images obtained by de-warping the images fromFIGS. 4A-B and combining the images to increase SNR in accordance withsome embodiments.

The above-described embodiments can be implemented in any of numerousways. One or more aspects and embodiments of the present disclosureinvolving the performance of processes or methods may utilize programinstructions executable by a device (e.g., a computer, a processor, orother device) to perform, or control performance of, the processes ormethods. In this respect, various inventive concepts may be embodied asa computer readable storage medium (or multiple computer readablestorage media) (e.g., a computer memory, one or more compact discs,optical discs, magnetic tapes, flash memories, circuit configurations inField Programmable Gate Arrays or other semiconductor devices, or othertangible computer storage medium) encoded with one or more programsthat, when executed on one or more computers or other processors,perform methods that implement one or more of the various embodimentsdescribed above. The computer readable medium or media can betransportable, such that the program or programs stored thereon can beloaded onto one or more different computers or other processors toimplement various ones of the aspects described above. In someembodiments, computer readable media may be non-transitory media.

The terms “program” or “software” are used herein in a generic sense torefer to any type of computer code or set of computer-executableinstructions that can be employed to program a computer or otherprocessor to implement various aspects as described above. Additionally,it should be appreciated that according to one aspect, one or morecomputer programs that when executed perform methods of the presentdisclosure need not reside on a single computer or processor, but may bedistributed in a modular fashion among a number of different computersor processors to implement various aspects of the present disclosure.

Computer-executable instructions may be in many forms, such as programmodules, executed by one or more computers or other devices. Generally,program modules include routines, programs, objects, components, datastructures, etc. that perform particular tasks or implement particularabstract data types. Typically the functionality of the program modulesmay be combined or distributed as desired in various embodiments.

Also, data structures may be stored in computer-readable media in anysuitable form. For simplicity of illustration, data structures may beshown to have fields that are related through location in the datastructure. Such relationships may likewise be achieved by assigningstorage for the fields with locations in a computer-readable medium thatconvey relationship between the fields. However, any suitable mechanismmay be used to establish a relationship between information in fields ofa data structure, including through the use of pointers, tags or othermechanisms that establish relationship between data elements.

The above-described embodiments can be implemented in any of numerousways. For example, the embodiments may be implemented using hardware,software or a combination thereof. When implemented in software, thesoftware code can be executed on any suitable processor or collection ofprocessors, whether provided in a single computer or distributed amongmultiple computers. It should be appreciated that any component orcollection of components that perform the functions described above canbe generically considered as a controller that controls theabove-discussed function. A controller can be implemented in numerousways, such as with dedicated hardware, or with general purpose hardware(e.g., one or more processor) that is programmed using microcode orsoftware to perform the functions recited above, and may be implementedin a combination of ways when the controller corresponds to multiplecomponents of a system.

Further, it should be appreciated that a computer may be embodied in anyof a number of forms, such as a rack-mounted computer, a desktopcomputer, a laptop computer, or a tablet computer, as non-limitingexamples. Additionally, a computer may be embedded in a device notgenerally regarded as a computer but with suitable processingcapabilities, including a Personal Digital Assistant (PDA), a smartphoneor any other suitable portable or fixed electronic device.

Also, a computer may have one or more input and output devices. Thesedevices can be used, among other things, to present a user interface.Examples of output devices that can be used to provide a user interfaceinclude printers or display screens for visual presentation of outputand speakers or other sound generating devices for audible presentationof output. Examples of input devices that can be used for a userinterface include keyboards, and pointing devices, such as mice, touchpads, and digitizing tablets. As another example, a computer may receiveinput information through speech recognition or in other audibleformats.

Such computers may be interconnected by one or more networks in anysuitable form, including a local area network or a wide area network,such as an enterprise network, and intelligent network (IN) or theInternet. Such networks may be based on any suitable technology and mayoperate according to any suitable protocol and may include wirelessnetworks, wired networks or fiber optic networks.

Also, as described, some aspects may be embodied as one or more methods.The acts performed as part of the method may be ordered in any suitableway. Accordingly, embodiments may be constructed in which acts areperformed in an order different than illustrated, which may includeperforming some acts simultaneously, even though shown as sequentialacts in illustrative embodiments.

All definitions, as defined and used herein, should be understood tocontrol over dictionary definitions, definitions in documentsincorporated by reference, and/or ordinary meanings of the definedterms.

The indefinite articles “a” and “an,” as used herein in thespecification and in the claims, unless clearly indicated to thecontrary, should be understood to mean “at least one.”

The phrase “and/or,” as used herein in the specification and in theclaims, should be understood to mean “either or both” of the elements soconjoined, i.e., elements that are conjunctively present in some casesand disjunctively present in other cases. Multiple elements listed with“and/or” should be construed in the same fashion, i.e., “one or more” ofthe elements so conjoined. Other elements may optionally be presentother than the elements specifically identified by the “and/or” clause,whether related or unrelated to those elements specifically identified.Thus, as a non-limiting example, a reference to “A and/or B”, when usedin conjunction with open-ended language such as “comprising” can refer,in one embodiment, to A only (optionally including elements other thanB); in another embodiment, to B only (optionally including elementsother than A); in yet another embodiment, to both A and B (optionallyincluding other elements); etc.

As used herein in the specification and in the claims, the phrase “atleast one,” in reference to a list of one or more elements, should beunderstood to mean at least one element selected from any one or more ofthe elements in the list of elements, but not necessarily including atleast one of each and every element specifically listed within the listof elements and not excluding any combinations of elements in the listof elements. This definition also allows that elements may optionally bepresent other than the elements specifically identified within the listof elements to which the phrase “at least one” refers, whether relatedor unrelated to those elements specifically identified. Thus, as anon-limiting example, “at least one of A and B” (or, equivalently, “atleast one of A or B,” or, equivalently “at least one of A and/or B”) canrefer, in one embodiment, to at least one, optionally including morethan one, A, with no B present (and optionally including elements otherthan B); in another embodiment, to at least one, optionally includingmore than one, B, with no A present (and optionally including elementsother than A); in yet another embodiment, to at least one, optionallyincluding more than one, A, and at least one, optionally including morethan one, B (and optionally including other elements); etc.

Also, the phraseology and terminology used herein is for the purpose ofdescription and should not be regarded as limiting. The use of“including,” “comprising,” or “having,” “containing,” “involving,” andvariations thereof herein, is meant to encompass the items listedthereafter and equivalents thereof as well as additional items.

In the claims, as well as in the specification above, all transitionalphrases such as “comprising,” “including,” “carrying,” “having,”“containing,” “involving,” “holding,” “composed of,” and the like are tobe understood to be open-ended, i.e., to mean including but not limitedto. Only the transitional phrases “consisting of” and “consistingessentially of” shall be closed or semi-closed transitional phrases,respectively.

The invention claimed is:
 1. A magnetic resonance imaging (MRI) system,comprising: a plurality of magnetics components including: a B₀ magnetconfigured to produce a main magnetic field B₀; at least one gradientcoil configured to, when operated, provide spatial encoding of emittedmagnetic resonance signals; at least one radio frequency (RF) componentconfigured to acquire, when operated, the emitted magnetic resonancesignals; and at least one controller configured to operate one or moreof the plurality of magnetics components in accordance with at least onepulse sequence having a diffusion-weighted gradient encoding periodfollowed by multiple echo periods during which magnetic resonancesignals are produced and detected, wherein a first of the multiple echoperiods corresponds to a first measurement of a line of k-space using afirst gradient polarity and a second of the multiple echo periodscorresponds to a second measurement of the line of k-space using asecond gradient polarity, the first gradient polarity opposing thesecond gradient polarity.
 2. The MRI system of claim 1, wherein the atleast one controller is further configured to reconstruct at least oneimage based, at, least in part, on the magnetic resonance signalsdetected during each of the multiple echo periods.
 3. The MRI system ofclaim 2, wherein the at least one pulse sequence further comprises an RFpulse followed by a readout period, wherein the readout period overlapsin time with the diffusion-weighted gradient encoding period.
 4. The MRIsystem of claim 3, wherein the at least one controller is furtherconfigured to: determine a phase of free induction decay during thereadout period; fit the determined phase to a linear model; andreconstruct the at least one image based, at least in part, on the fitphase to correct image blurring due to drift in the main magnetic fieldB₀.
 5. The MRI system of claim 1, wherein reconstructing the at leastone image comprises: reconstructing a first plurality of images based,at least in part, on the magnetic resonance signals detected during thefirst echo period; reconstructing a second plurality of images based, atleast in part, on the magnetic signals detected during the second echoperiod; de-warping the first plurality of images and the secondplurality of images; and combining the de-warped first plurality ofimages and the second plurality of images to reconstruct the at leastone image.
 6. The MRI system of claim 1, wherein the diffusion-weightedgradient encoding period includes a diffusion-weighted gradient pulsewith asymmetrical attack and decay edges such that thediffusion-weighted gradient pulse is not trapezoidal shaped.
 7. The MRIsystem of claim 6, wherein the attack edge of the diffusion-weightedgradient pulse has a slope that varies.
 8. The MRI system of claim 1,wherein: the second echo period immediately follows the first echoperiod, the at least one pulse sequence further comprises an RF pulsefollowed by a readout period, wherein the readout period overlaps intime with the diffusion-weighted gradient encoding period, and thediffusion-weighted gradient encoding period includes adiffusion-weighted gradient pulse with asymmetrical attack and decayedges such that the diffusion-weighted gradient pulse is not trapezoidalshaped, wherein the attack edge of the diffusion-weighted gradient pulsehas a slope that varies.
 9. The MRI system of claim 8, wherein the atleast one controller is further configured to: reconstruct a firstplurality of images based, at least in part, on the magnetic resonancesignals detected during the first echo period; reconstruct a secondplurality of images based, at least in part, on the magnetic signalsdetected during the second echo period; de-warp the first plurality ofimages and the second plurality of images; combine the de-warped firstplurality of images and the second plurality of images to producecombined images; determine a phase of free induction decay during thereadout period; fit the determined phase to a linear model; andreconstruct at least one image based, at least in part, on the fit phaseand the combined images.
 10. The MRI system of claim 1, wherein the B₀magnet is configured to produce a B₀ field having a strength equal to orless than 0.2T and greater than or equal to 0.1T.
 11. The MRI system ofclaim 1, wherein the B₀ magnet is configured to produce a B₀ fieldhaving a strength equal to or less than 0.1T and greater than or equalto 50mT.
 12. The MRI system of claim 1, wherein the B₀ magnet isconfigured to produce a B₀ field having a strength equal to or less than50mT and greater than or equal to 20mT.
 13. A computer-implementedmethod of operating a magnetic resonance imaging (MRI) system to performdiffusion weighted imaging, the MRI system including a plurality ofmagnetics components including a B₀ magnet configured to produce a mainmagnetic field B₀, at least one gradient coil configured to, whenoperated, provide spatial encoding of emitted magnetic resonancesignals, and at least one radio frequency (RF) component configured toacquire, when operated, the emitted magnetic resonance signals, themethod comprising: controlling one or more of the plurality of magneticscomponents in accordance with at least one pulse sequence having adiffusion-weighted gradient encoding period followed by multiple echoperiods during which magnetic resonance signals are produced anddetected, wherein a first of the multiple echo periods corresponds to afirst measurement of a line of k-space using a first gradient polarityand a second of the multiple echo periods corresponds to a secondmeasurement of the line of k-space using a second gradient polarity, thefirst gradient polarity opposing the second gradient polarity.
 14. Thecomputer-implemented method of claim 13, wherein the second echo periodimmediately follows the first echo period, and wherein-the methodfurther comprises: reconstructing a first plurality of images based, atleast in part, on the magnetic resonance signals detected during thefirst echo period; reconstructing a second plurality of images based, atleast in part, on the magnetic signals detected during the second echoperiod; de-warping the first plurality of images and the secondplurality of images; and combining the de-warped first plurality ofimages and the second plurality of images to reconstruct at least oneimage.
 15. The computer-implemented method of claim 13, wherein the atleast one pulse sequence further comprises an RF pulse followed by areadout period, wherein the readout period overlaps in time with thediffusion-weighted gradient encoding period, and wherein the methodfurther comprises: determining a phase of free induction decay duringthe readout period; fitting the determined phase to a linear model; andreconstructing at least one image based, at least in part, on the fitphase to correct image blurring due to drift in the main magnetic fieldB₀.
 16. The computer-implemented method of claim 13, wherein thediffusion-weighted gradient encoding period includes adiffusion-weighted gradient pulse with an attack edge having a slopethat varies.
 17. A non-transitory computer-readable medium encoded witha plurality of instructions that, when executed by at least one computerprocessor, cause the at least one computer processor to perform a methodof operating a magnetic resonance imaging (MRI) system to performdiffusion weighted imaging, the MRI system including a plurality ofmagnetics components including a B₀ magnet configured to produce alow-field main magnetic field B₀, at least one gradient coil configuredto, when operated, provide spatial encoding of emitted magneticresonance signals, and at least one radio frequency (RF) componentconfigured to acquire, when operated, the emitted magnetic resonancesignals, the method comprising: controlling one or more of the pluralityof magnetics components in accordance with at least one pulse sequencehaving a diffusion-weighted gradient encoding period followed bymultiple echo periods during which magnetic resonance signals areproduced and detected, wherein a first of the multiple echo periodscorresponds to a first measurement of a line of k-space using a firstgradient polarity and a second of the multiple echo periods correspondsto a second measurement of the line of k-space using a second gradientpolarity, the first gradient polarity opposing the second gradientpolarity.
 18. The non-transitory computer-readable medium of claim 17,wherein the second echo period immediately follows the first echo periodthe method further comprises: reconstructing a first plurality of imagesbased, at least in part, on the magnetic resonance signals detectedduring the first echo period; reconstructing a second plurality ofimages based, at least in part, on the magnetic signals detected duringthe second echo period; de-warping the first plurality of images and thesecond plurality of images; and combining the de-warped first pluralityof images and the second plurality of images to reconstruct at least oneimage.
 19. The non-transitory computer-readable medium of claim 17,wherein the at least one pulse sequence further comprises an RF pulsefollowed by a readout period, wherein the readout period overlaps intime with the diffusion-weighted gradient encoding period, and whereinthe method further comprises: determining a phase of free inductiondecay during the readout period; fitting the determined phase to alinear model; and reconstructing at least one image based, at least inpart, on the fit phase to correct image blurring due to drift in themain magnetic field B₀.
 20. The non-transitory computer-readable mediumof claim 17, wherein the diffusion-weighted gradient encoding periodincludes a diffusion-weighted gradient pulse with an attack edge havinga slope that varies.